Factory-on-a-chip for production of biologically derived medicines/biopharmaceuticals/biologics/ biotherapeutics

ABSTRACT

The present invention provides for a fully integrated microfluidic system capable of producing single-dose amounts of biotherapeutics at the point-of-care wherein protein production, purification and product harvest are all integrated as a single microfluidic device which is portable and capable of continuous-flow production of biotherapeutics at the microscale using a cell-free reaction system.

CROSS REFERENCE TO RELATED APPLICATION

The present application claims priority to U.S. Provisional PatentApplication No. 62/516,161 filed on Jun. 7, 2017, the contents of whichare hereby incorporated by reference herein.

GOVERNMENT RIGHTS IN INVENTION

This invention was made with government support under Grant NumberN66001-13-C-4023 awarded by the Defense Advanced Research ProjectsAgency (DARPA). The government has certain rights in the invention.

FIELD OF THE INVENTION

The present invention relates to protein manufacturing and, moreparticularly, to an integrated microfluidic bioprocessing system foron-demand production or manufacturing of proteins for point-of-caredelivery.

BACKGROUND THE INVENTION

Production of biologically-derived medicines or biotherapeutics involvesa large scale (>10,000 L) process chain which includes large volumeseparation, purification, formulation, packaging and distribution¹⁻³.The major cost is in the maintenance of living organism from which thesebiotheraputics are harvested and the cold chain required to keep theproduct stable until it reaches the patient. To counter the complexitiesand expense of maintaining living organisms for biotherapeutics, recentefforts have seen the use of cellular extracts as a source forbiomanufacuring. This has helped reduce production time from weeks to amatter of hours⁴. These extracts contain a majority of the cellularmachinery that are capable of producing properly folded and functionalactive biotherapeutics⁴. Recently, cell extract from differentbiosystems (Mammalian Chinese Hampster Ovary (CHO) cells, yeast and E.coli) have become commercially available. The availability of cell-freeextracts has made miniaturization and automation of protein purificationa possibility.⁵⁻⁸ However, the miniaturization and automation stillremain immature, some of these lack a purification chain and the proteinyield is low, hence may not be well suited for point-of-careapplications.

The manufacturing process for biotherapeutics relies heavily onlarge-scale fermentation batches that require frequent monitoring toensure robustness and product quality. However, as personalizedmedicines and single-use device technologies are becoming increasinglyimportant, there is a growing need for flexible, scalable, affordableand portable systems that offer manufacturing options.

Thus, there is a need to provide for a new portable platform formanufacturing biotherapeutics at the point-of-care wherein the portableplatform would operate in mobile units (e.g. ambulance), patientbed-sides, pharmacies, resource limited areas, acute emergencies andbattlefields.

SUMMARY OF THE INVENTION

The present invention provides for a fully integrated microfluidicsystem capable of producing single-dose amounts of biotherapeutics atthe point-of-care wherein protein production, purification and productharvest are all integrated as a single microfluidic device which isportable and capable of continuous-flow production of biotherapeutics atthe microscale using a cell-free reaction system.

In one aspect the present invention provides for a portable“factory-on-a-chip” comprising three primary components, wherein thecomponents comprise a bioreactor unit, a mixer/debubbler andpurification unit, wherein the purification unit comprises amultiplicity of chromatography columns. This setup will serve as apersonalized medical device kit with the ability to prepare smallquantities of biotherapeutics on-demand.

In yet another aspect, the present invention provides for afactory-on-a-chip microfluidic device comprising:

(i) a microfluidic bioreactor unit equipped with a continuous collectionchannel for synthesizing a crude protein in a reaction within themicrofluidic bioreactor;

(ii) a microfluidic mixer/de-bubbler unit communicatively connected tothe microfluidic bioreactor unit to dilute the crude protein and removeany air bubbles during mixing; and

(iii) a microfluidic purification unit communicatively connected to themicrofluidic mixer/de-bubbler unit comprising at least one purificationcolumn for capturing the crude protein and providing a purified protein,wherein the purification unit is preferably connected to sensors formonitoring pH, ionic strength, UV-Vis absorbance, fluorescence, lightscatter and or circular dichroism for testing of the purified protein.Protein analysis is preferably conducted in an analytical module by atleast one process analytical technology (PAT) sensor to analyze andmonitored pH, ionic strength, UV-Vis absorbance, fluorescence, lightscatter, and/or circular dichroism.

Preferably, units (i), (ii) and (ii) are stacked together to form asingle unit having a dimensional length of about 100 mm to 150 mm and awidth perpendicular to the length of about 40 mm to about 90 mm.

In some embodiments, the mixer/de-bubbler comprises a porous membrane toeliminate bubbles and an addition of at least one microfluidic valve tooptimize flow. The microfluidic valves may be integrated either as partof the chip or as an external component within a process channel toensure that the process flow is effectively controlled

In a further aspect, the present invention provides for an integrateddevice comprising a reactor, mixer and purification chip connectedtogether as one platform chip. For in-line quality control additionalsensors are include along the production line of the process includingsensors to measure pressure, temperature, pH, dissolved oxygen sensorand/or UV detector to produce a scalable amount of a therapeuticalprotein for point of care administration.

The factory-on-a-chip microfluidic device of the present inventionpreferably has from about 4 to 8 purification micro-columns positionedin the microfluidic purification unit. The purification micro-columnscomprise microscale channels for moving a volume ranging from about25-200 μL. The microscale channels comprise chromatography resin forcapturing the crude protein. Preferably the chromatography resin is animmobilized metal affinity resin and/or an ion exchange resin. Furtherthe purification micro-columns accommodate solutions for an elutionbuffer for harvesting the purified protein. In one embodiment, themicro-columns are fabricated of three polymeric layers comprising a toplayer, a middle layer comprising the microscale channels and a baseplate. Preferably, the top layer is about 1 to about 2 mm thick, themiddle layer about 0.75 to about 1.25 mm comprising the a micro-channelto accommodate chromatography resin and the base plate is about 1 toabout 2 mm.

The microfluidic bioreactor comprises cell extracts and reagents forexpression of the crude protein. Such cell extracts comprise acombination of cytoplasmic and/or nuclear components from cellscomprising reactants for protein synthesis, transcription, translation,DNA replication.

The integrated device may further comprise a processor for controllingand/or monitoring timing, temperature and other parameters necessary foroptimizing the production and purification of the synthesized proteinsto provide a sufficient amount of or a therapeutic dosage of thesynthesized protein. Such length of time in the microfluidic bioreactorand/or purification unit may be used to affect the potency and/oractivity of the synthesized protein.

In another aspect, the present invention provides for method ofpreparing and administering a therapeutic protein on demand to asubject, the method comprising:

-   (a) synthesizing the therapeutic protein with a microfluidic factory    on a chip comprising:    -   (i) a microfluidic bioreactor unit equipped with a continuous        collection channel for a synthesizing a crude therapeutic        protein in a reaction within the microfluidic bioreactor and at        least one process analytical technology (PAT) sensor        (pH/dissolved-oxygen/redox) for monitoring conditions during the        reaction;    -   (ii) a microfluidic mixer/de-bubbler unit communicatively        connected to the microfluidic bioreactor to dilute the crude        therapeutic protein and remove any air bubbles during mixing;        and    -   (iii) a microfluidic purification unit communicatively connected        to the microfluidic mixer/de-bubbler unit comprising at least        one purification column capturing the crude therapeutic protein        and providing a purified therapeutic protein, wherein the        microfluidic purification unit is preferably connected to        sensors for monitoring pH, ionic strength, UV-Vis absorbance,        fluorescence, light scatter and or circular dichroism of the        purified therapeutic protein; and-   (b) administering the purified therapeutic protein to the subject in    a sufficient amount of time to maintain the viability of the    purified therapeutic protein.

In another aspect, the present invention provides for on-demandproduction of a therapeutic protein, wherein the therapeutic proteinexhibits increased potency due to the timely synthesis and substantiallyimmediate delivery of protein. Preferably, the newly synthesizedproteins are delivered to a patient within one hour, to one day, to twoweeks. Any refrigeration is at a temperature above freezing from 0 to 6°C. Any freezing of the proteins is preferably a single event withtemperatures ranging from about −2° C. to about −10° C.

Additional advantages, aspects, and features of the invention will beset forth in part in the description which follows and in part willbecome apparent to those having ordinary skill in the art uponexamination of the following or may be learned from practice of theinvention. The aspects and advantages of the invention may be realizedand attained as particularly pointed out in the appended claims.

BRIEF DESCRIPTION OF THE FIGURES

FIG. 1 shows a 3-D image of the Factory-on-a-chip.

FIG. 2 shows external and internal components of the device. FIG. 2Ashows an external box for inserting the bioreactor unit consisting ofthe reactor cassette and product vial.

FIG. 2B shows a bioreactor cassette which holds the fully integratedmicrofluidic chip and sensors. The disposable Bioreactor cassettecontains the lyophilized cell extracts and reagents needed forexpression and the microfluidics for purification of the desiredtherapeutic protein. The non-disposable box, the size of a videocassette player considered to be an analytical module (150), containsthe necessary pumps, buffers for purification and analytics for realtime quality control wherein testing analytics in the analytic modulecomprises at least one process analytical technology (PAT) sensor formonitoring pH, pressure, temperature, dissolved-oxygen, redoxconditions, ionic strength, UV-Vis absorbance, fluorescence, lightscatter, and/or circular dichroism.

The bioreactor cassette is inserted into the box and within a few hours,the G-CSF will be deposited in the product vial available for immediatedelivery to the patient.

FIG. 3 shows the bioreactor cassette pieces which show (from top tobottom) the casing, fluid connectors, microfluidic chips and PAT sensorsfor real time monitoring of the bioprocess.

FIG. 4 shows again the Factory-on-a-chip device which contains thebioreactor, mixer/debubbler and purification unit.

FIG. 5 shows the process chain showing the following (I) Proteinexpression: GFP expression is imaged after 4 h at 30° C. on ashaker-incubator in the bioreactor. (II) Protein capture: GFP, postexpression, was collected, diluted and passed through an immobilizedmetal affinity chromatography resin (IMAC). The IMAC resin was packedinside a multiple column microfluidic channel. The captured protein isseen in lane 2 of the high sensitivity silver stain gel. (III) Proteinpurification: the eluted sample from the IMAC capture step was thenpassed through an ion-exchange resin (Q-Sepharose FF). The sample isseen in lane 3 has lesser impurity bands compared to those observed inlane 2. Lane 3 bands are also comparable to the purified GFP standardspurchased from Thermo Scientific Inc.

FIG. 6 shows one design of a multiple column microfluidic chromatographysystem applicable for the device of the present invention.

FIG. 7 shows another design of a multiple column microfluidicchromatography system applicable for the device of the presentinvention.

FIG. 8 shows the purification product using the microfluidicChromatography chip of FIG. 6. Photo 1. Image taken after loading theHisPur Cobalt resin (Tolan beads): The flow was generated manually usinga 3 mL syringe. Photo 2. Image taken after loading with 1 mL dilutedGFP-Harvest (5× dilution of raw lysate) and then flowing through a washbuffer (3 mL) (5 mM imidazole, 1×PBS, pH 7.2). Photo 3(A) Image takenhalf way through elution step. (With a total of 3 mL elution buffer:divided into two collection vials of about 1.5 mL each) Photo 3(B)Elution buffer (150 mM imidazole, 1×PBS, pH 7.2). Image taken postelution. Most of the protein elutes in the first 1.5 mL electionfraction and did not leave much protein in the column. Photo 4. Flowthrough from stage 2. It is believed that controlled pumping the lysateinto the column at an efficiently monitored flow rate would improve thebinding. The other option would be to improve the packing efficiency ofthe channels.

FIG. 9 shows the purification product using the microfluidicChromatography chip of FIG. 7. Photo 1. Image taken after loading theHisPur Cobalt resin (Tolan beads): The flow was generated manually usinga 3 mL syringe. Photo 2. Image taken after loading with 1 mL dilutedGFP-Harvest (5× dilution of raw lysate) and the then flowing through awash buffer (3 mL) (5 mM imidazole, 1×PBS, pH 7.2). Photo 3(A) Imagetaken half way through elution step. (With a total of 3 mL elutionbuffer: divided into two collection vials of about 1.5 mL each). Photo3B Elution buffer (150 mM imidazole, 1×PBS, pH 7.2). Image taken postelution. Most of the protein elutes in the first 1.5 mL electionfraction and did not leave much protein in the column. Photo 4 shows GFPflow through from stage 2. Slightly better controlled pumping of thelysate into the column with a monitored flow rate slightly improved thebinding of GFP. The first pass flow through was also recirculated oncemore through the column which improved the efficiency of binding.

FIG. 10 show a device design sketch; A) 3D sketch in designed usingSketchUp Pro. B) These columns are made up of three layers of polymethylmethacrylate (PMMA); bottom base plate layer (each 1 mm thick), middlechannel layer and top inlet/outlet layer (1.5 mm thick). The top layercontains a larger circular slot towards the outlet for PTFE frits. PTFEfrits were added post bonding. This array consists of 5 columns of 100μL volume. C) This picture of the customizable microscale column device(μCol) shows an array of columns with varied resin capacities (25-200μL, from left to right) displaying the versatility of this system.

FIG. 11 shows acetone injections for column validations. A) 1% Acetoneinjections performed on each of the different volume (25-200 μL)columns, where the flow rate was 0.2 mL/min. B) 1% Acetone injectionsperformed on each 100 μL column, where the flow rate was 0.5 mL/min.These validation experiments demonstrate the manufacturing consistencyacross tested columns. μCol validation chart lists the theoreticalplates and asymmetrical ratios for His-cobalt columns tested atdifferent flow rates. C) Table presents the micro-column validation datafor different column volumes, showing theoretical plates andasymmetrical ratio calculated using the HPLC software. Methods adoptedfor the column connections to the HPLC and other lab methods are shownand explained in FIG. 17.

FIG. 12 A) 3D design of the one-frit column, where the PTFE frit isplaced at the channel outlet. B) 3D design of the two-frit columns, witha PTFE frit placed at the channel inlet and outlet.

FIG. 12 Cont. shows the computational model results are plotted forcomparisons between C) One-frit columns, D) One-frit versus the two-fritcolumns. Through these models the one-frit system produced slightlybetter profiles compared to the two-frit channels, E) Different fritthicknesses (1 to 2 mm) were tested by computational modeling, whichrevealed that column performance is dependent on frit thicknesses.

FIG. 13 shows binding and elution profiles for G-CSF purification onmulti-volume arrayed μCol device. A) G-CSF binding peaks observed inμCols loaded with 0.3 mL of G-CSF harvest. B) G-CSF elution peaksobserved as the elution buffer is introduced into the columns. These areelution peaks seen for the 0.3 mL harvest; each individual run showedsharp peaks of protein. Tested on different sets of columns. The μCol isconnected to the HPLC system like a conventional column setup (FIG. 17,show the image of setup). C) Silver stained SDS-PAGE gel images, wheretwo chips A and B were used to purify 0.3 mL G-CSF harvest. The harvestand elution band are consistent between repeats. D) Western blots showthe G-CSF protein bands for each of the eluted samples, harvest andblank (without DNA), and values are presented in Table E.

FIG. 14 shows binding, wash and elution profiles for G-CSF purificationon the single volume μCol device. A) G-CSF binding peaks observed inμCols loaded with 0.3 mL of G-CSF harvest. B) The following stepinvolves washing the column to remove any impurities during the bindingstep. Wash peaks observed on the HPLC. C) G-CSF elution peaks observedas the elution buffer is introduced into the columns. These are elutionpeaks seen for the 0.3 mL harvest set where 4 individual runs showedsharp peaks of protein. D) G-CSF elution peaks observed as the elutionbuffer is introduced into the columns. These are elution peaks seen forthe 0.5 mL harvest set where 3 individual runs showed sharp peaks ofprotein. E) Shows a comparison between G-CSF elution peaks between theμCol and 1 mL ThermoFisher Scientific (Thermo) column. The μCol has amuch sharper peak compared to the Thermo column. Collected volume forthe μCol was 0.5 mL vs 2.3 mL for the Thermo column. The μCol isconnected to the HPLC system like a conventional column setup (image inFIG. 17). F) Silver stained SDS-PAGE gel images, for 0.3 mL G-CSFharvest, elutions showing consistency between repeats. Also compared the1 mL harvest samples tested in both the μCol and Thermo pre-packedcolumn. G) 0.5 mL G-CSF harvest, elutions showing consistency betweenrepeats and slight impurities are noticed on the Thermo pre-packedcolumn in comparison to the μCol. Arrows mark the impurities seen onlywithin the Thermo column sample. H) Provides the concentrations ofprotein post purification for each of the tested harvest volumes.

FIG. 15 shows that the method for bonding PMMA chips was standardizedand provides a rapid prototyping technique for mass production of μCol.A) PMMA chips were doused in 100% ethanol, then sandwiched togetherbetween aluminum plates and silicone sheets. This sandwiched set is thengently placed between two heated platens. B) The platens are customfitted to a Carver® Press (Carver Hydraulic Press Model M), whichsqueezes the platens together. C) The controller box regulates thetemperature on each heated platen, the set point temperature is 80° C.D) The pressure gauge is at 2500 psi.

FIG. 16 shows the placing PTFE frit inserts and resin packing methods.A) Process for adding PTFE frits post bonding. 1) Frits were simplyplaced into the slot post-bonding, 2) Luer lock fittings were glued(cyanoacrylate 2075) on top to hold the frits in place, 3) Glued devicesset overnight and stored in a clean cabinet until packed. B) The columnpacking was optimized to work specifically for μCol designs. The processflow schematic has the following steps. 1) 20% ethanol (10 mL syringe)was pushed through the device (0.5 mL/min flow rate), this removes anyair-bubbles in the device. The changes in pressure are monitored in realtime while His-beads were packed at a constant flow rate of 0.5 mL/min.After bead loading, 10-15 column volumes of 20% ethanol were pushedthrough the packed device at 0.5 mL/min, to ensure the tight packing ofbeads. Post packing, devices were stored at 4° C. until used forvalidation and purification experiments.

FIG. 17 shows images of the device setup. A) The μCol is assembledin-line with the Labsmith™ microfluidic platform and the Senserion® flowsensor, which enables monitoring bead packing parameters in real-time.(Process flow is described in FIG. 11). B) Column is attached to theHPLC to implement a pre-saturation wash, with 10 mM imidazole buffer at0.5 mL/min, prior to loading the protein. Protein was loaded on thecolumn using an externally connected syringe pump at a rate of 0.2mL/min. This was followed by a wash step to remove impurities andfinally an elution step to collect the protein for subsequent proteinanalysis. Protein analysis is preferably conducted in an analyticalmodule by at least one PAT sensor to analyze and monitored pH, ionicstrength, UV-Vis absorbance, fluorescence, light scatter, and/orcircular dichroism.

FIG. 18 shows bead packing pressure and flow rate measurements in realtime. 1-2 mL ethanol (10 mL syringe) was pushed through the device (0.5mL/min flow rate) to wet the surface and remove any air bubbles prior toadding the beads. The pressures and fluidic flow were monitored in realtime while His-beads collect inside the column. A) Packing pressureswere recorded to be between 20-40 kPa (˜3-6 psi) with operationpressures reaching a maximum of 50 kPas (˜7.2 psi); when B) flow ratesmaintained at around 0.5 mL/min. 10-15 column volumes of 20% ethanol waspushed through the packed device at 0.5 mL/min, to ensure the tightpacking of beads.

DETAILED DESCRIPTION OF THE INVENTION

The present invention is particularly suited for the on-demandmanufacturing of therapeutic proteins that are suitable for on-demandsynthesis and for direct delivery to a patient. Therefore, the presentinvention will be primarily described and illustrated in connection withthe manufacturing of therapeutic proteins. However, the presentinvention can also be used to manufacture any type of protein, includingtoxic proteins, proteins with radiolabeled amino acids, unnatural aminoacids, etc. Further, the present invention is particularly suited forthe on-demand manufacturing of proteins using cell-free expression, andthus the present invention will be described primarily in the context ofcell-free protein expression. However, the present invention can also beused in connection with cell-based protein expression.

Definitions

“Microfluidic chip” means at least one microfluidic channel etched ormolded into a material (e.g., glass, silicon or polymers such PDMS(polydimethylsiloxane) and polymethyl methacrylate (PMMA). Themicro-channels are connected together in order to achieve a desiredfeature (e.g., mix, pump, sort, or control the biochemical environment).The “cross-sectional dimension” of the channel is measured perpendicularto the direction of fluid flow within the channel. Thus, some or all ofthe fluid channels in microfluidic embodiments of the invention may havemaximum cross-sectional dimensions less than 2 mm, and in certain cases,less than 1 mm. In one set of embodiments, all fluid channels containingembodiments of the invention are microfluidic or have a largest crosssectional dimension of no more than 2 mm or 1 mm. In certainembodiments, the fluid channels may be formed in part by a singlecomponent (e.g. an etched substrate or molded unit). Of course, largerchannels, tubes, chambers, reservoirs, etc. can be used to store fluidsand/or deliver fluids to various components or systems of the invention.

“Comprise(s),” “include(s),” “having,” “has,” “can,” “contain(s),” andvariants thereof, as used herein, are intended to be open-endedtransitional phrases, terms, or words that do not preclude thepossibility of additional acts or structures. The singular forms “a,”“and” and “the” include plural references unless the context clearlydictates otherwise. The present disclosure also contemplates otherembodiments “comprising,” “consisting of” and “consisting essentiallyof,” the embodiments or elements presented herein, whether explicitlyset forth or not.

The term “cell-free” as used herein refers to an “in vitro” combinationof reactants capable of performing reactions occurring in a cellularenvironment, in a mixture where the reactants are comprised outside thecellular environment. Cell-free systems, by definition, do not includewhole cells capable of replicating but its components are typicallyderived from a cell and comprise a combination of cytoplasmic and/ornuclear components from cells comprising reactants for proteinsynthesis, transcription, translation, DNA replication and/or additionalbiological reactions occurring in a cellular environment identifiable bya person skilled in the art.

“Affinity” and “binding affinity” as used interchangeably herein referto the tendency or strength of binding of the binding member to theanalyte. For example, the binding affinity may be represented by theequilibrium dissociation constant (K_(D)), the dissociation rate(k_(d)), or the association rate (k_(a)).

“Label” or “detectable label” as used interchangeably herein refers to amoiety attached to a specific binding member or analyte to render thereaction between the specific binding member and the analyte detectable,and the specific binding member or analyte so labeled is referred to as“detectably labeled.” A label can produce a signal that is detectable byvisual or instrumental means. Various labels include: (i) a tag attachedto a specific binding member or analyte by a cleavable linker; or (ii)signal-producing substance, such as chromagens, fluorescent compounds,enzymes, chemiluminescent compounds, radioactive compounds, and thelike. Representative examples of labels include moieties that producelight, e.g., acridinium compounds, and moieties that producefluorescence, e.g., fluorescein. Other labels are described herein. Inthis regard, the moiety, itself, may not be detectable but may becomedetectable upon reaction with yet another moiety. Use of the term“detectably labeled” is intended to encompass such labeling.

“Microparticle(s)” and “microbead(s)” are used interchangeably hereinand refer to a microbead or microparticle that is allowed to occupy orsettle in an array of wells, such as, for example, in an array of wellsin a detection module. The microparticle and microbead may contain atleast one specific binding member that binds to an analyte of interestand at least one detectable label. Alternatively, the microparticle andmicrobead may containing a first specific binding member that binds tothe analyte and a second specific binding member that also binds to theanalyte and contains at least one detectable label.

Protein production, purification and product harvest are all integratedas a single microfluidic device, referred to as a ‘Factory-on-a-chip’ asshown in FIG. 1. The Factory-on-a-chip microfluidic device includes amicrofluidic bioreactor (100) equipped with a continuous collectionchannel for the target biotherapeutic and at least one PAT sensors(including pH, dissolved-oxygen, redox, ionic strength, UV-Visabsorbance, fluorescence, light scatter, and/or circular dichroism)during the reaction, a microfluidic mixer/de-bubbler unit (110) iscommunicatively connected to the bioreactor to dilute the crude proteinharvest and get rid of any air bubbles during the mixing process.Initial fabrication tests for the mixer/de-bubbler were successfullyachieved using a porous membrane which is able to eliminate bubbles.FIGS. 2 and 3 provide for additional components for enclosing thefactory on a chip unit including an external box, device holder,integrated sensors, etc. This setup will serve as a personalized medicaldevice kit with the ability to prepare small quantities ofbiotherapeutics.

The porous membrane used in the mixer/de-bubbler can be fabricated fromany porous polymeric material that reduces bubbles including, polyester,polypropylene, nylon, fluorocarbon polymers such aspolytetrafluoroethylene, polyethylene, and polysulfone, and compositescomprising one or more of such materials.

Microfluidic purification unit (120) in FIG. 1 is communicativelyconnected to the microfluidic mixer/de-bubbler unit mixer device andcontain a modular chip based purification column or columns for proteincapture, buffer-exchange and polishing the protein harvest.Chromatography resins are included in the chromatography columns (130)and selected for chromatography resin packing efficiency and columnefficiency. Product collection from the columns is collected in chip(140). Notably the purification module can be connected to an analyticalmodule (150, FIG. 2) for product characterization wherein conditions andanalysis of the produced product in both the purification module andanalytical module can be monitored and determined by sensors includingpH, ionic strength, UV-Vis absorbance, fluorescence, light scatter,and/or circular dichroism.

“Chromatography resin” refers herein to a solid phase that selectivelyor preferentially binds one or more proteins from the source liquid. Inthe practice of the invention, such “chromatography resins” can beselected from any of the groups of resins commonly described asaffinity, ion exchange and ion capture resins. The resins need onlypossess a chemistry or an associated ligand that will selectively orpreferentially capture a substance of interest from the source liquid.Useful chromatography resins typically comprise a support and one ormore ligand(s) bound thereto that provide(s) the selective orpreferential binding capability for the target substance(s) of interest.Useful supports include, by way of illustrative example, polysaccharidessuch as agarose and cellulose, organic polymers such as polyacrylamide,methylmethacrylate, and polystyrene-divinylbenzene copolymers such asfor example Amberlite© resin, commercially available from Rohm & HaasChemical Co., Philadelphia, Pa. It should be recognized that althoughthe term “resin” is commonly used in the art of chromatography, it isnot intended herein to imply that only organic substrates are suitablefor resin substrate use, since inorganic support materials such asmetals, silica and glasses have utility as well. In the practice of thepresent invention, the resin may be in the form of beads which aregenerally spherical, or alternatively the resin may be usefully providein particulate or divided forms having other regular shapes or irregularshapes. The resin may be of porous or nonporous character, and the resinmay be compressible or incompressible. Preferred resins will bephysically and chemically resilient to the conditions employed in thepurification process including pumping, temperatures, pH, and otheraspects of the liquids employed. The resin as employed in the practiceof the present invention is preferably of regular generally sphericalshape, nonporous and incompressible.

“Affinity chromatography resin” or “affinity resin” refers to achromatography resin that comprises a solid support or substrate withaffinity ligands bound to its surfaces. Illustrative, non-limitingexamples of suitable affinity chromatography resins include sphericalbeads with affinity ligands bound to the bead surfaces, wherein thebeads are formed of cellulose, poly-styrene-divinylbenzene copolymer,polymethylmethacrylate, or other suitable material.

Ion exchange chromatography resin” or “ion exchange resin” refers to asolid support to which are covalently bound ligands that bear a positiveor negative charge, and which thus has free counterions available forexchange with ions in a solution with which the ion exchange resin iscontacted.

“Cation exchange resins” refers to an ion exchange resin with covalentlybound negatively charged ligands, and which thus has free cations forexchange with cations in a solution with which the resin is contacted. Awide variety of cation exchange resins, for example, those wherein thecovalently bound groups are carboxylate or sulfonate, are known in theart. Commercially available cation exchange resins includeCMC-cellulose, SP-Sephadex®, and Fast S-Sepharose® (the latter two beingcommercially available from Pharmacia).

“Anion exchange resins” refers to an ion exchange resin with covalentlybound positively charged groups, such as quaternary amino groups.Commercially available anion exchange resins include DEAE cellulose, QAESephadex, and Fast Q Sepharose® (the latter two being commerciallyavailable from Pharmacia).

FIG. 5 shows effective results using an immobilized metal affinity resinand an ion exchange resin. Immobilized metal affinity chromatography(IMAC) is a specialized variant of affinity chromatography where theproteins or peptides are separated according to their affinity for metalions that have been immobilized by chelation to an insoluble matrix. AtpH values around neutral, the amino acids histidine, tryptophan, andcysteine form complexes with the chelated metal ions (e.g., Zn2+, Cu2+,Cd2+, Hg2+, Co2+, Ni2+, and Fe2+). This technique is especially suitedfor purifying recombinant proteins as poly-histidine fusions and formembrane proteins and protein aggregates where detergents orhigh-ionic-strength buffers are required.

FIGS. 6 and 7 shows two different types of multiple column microfluidicchromatography systems. FIG. 6 provides for a system including checkvalves and a spin column frit used as a collection chamber. FIG. 7 showsthat the system is connected to an inlet and outlet for controlling thelysate into the system.

FIGS. 8 and 9 shows the results of using the multiple columnmicrofluidic chromatography systems of FIGS. 6 and 7 respectively. Theresults shown in FIG. 9 show that controlled flow of the lysatecontaining the proteins into the columns provides for increased bindingof the proteins to the chromatography resin. Also recirculation isbeneficial for recapturing product.

Protein Expression in In Vivo and Cell-Free Systems

A protein is expressed in three main steps: replication, transcriptionand translation. DNA multiplies to make multiple copies by a processcalled replication. Transcription occurs when the double-stranded DNA isunwound to allow the binding of RNA polymerase producing messenger RNA(mRNA). Transcription is regulated at various levels by activators andrepressors, and also by chromatin structure in eukaryotes. Inprokaryotes, no special post-transcriptional modification of mRNA isrequired. However, in eukaryotes, mRNA is further processed to removeintrons (splicing), to add a ‘cap’ (M7 methyl-guanosine) at the 5′ endand to add multiple adenosine ribonucleotides at the 3′ end of mRNA togenerate a poly(A) tail. The modified mRNA is then translated.

The translation or protein synthesis is also a multi-step process withInitiation, Elongation and Termination steps and is similar in bothprokaryotes and eukaryotes. The difference is that in eukaryotes,proteins may undergo post-translational modifications, such asphosphorylation or glycosylation. The translation process requirescellular components such as ribosomes, transfer RNAs (tRNA), mRNA andprotein factors as well as small molecules like amino acids, ATP, GTPand other cofactors.

The difference between in vivo and in vitro (cell-free) proteinexpression is that in cell-free expression, the cell wall and the nucleiare no longer present.

Cell-Free Protein Expression

To obtain the cell extract for cell-free protein expression, cells (E.coli, wheat germ, mammalian cells) are subjected to cell lysis followedby separation of the cell wall and nuclear DNA. The desired protein issynthesized by adding a DNA or mRNA template into the cell extracttogether with a reaction mix comprising of biological extracts and/ordefined reagents. The reaction mix is comprised of amino acids,nucleotides, co-factors, enzymes and other reagents that are necessaryfor the synthesis, e.g. ribosomes, tRNA, polymerases, transcriptionalfactors, etc. When DNA is used as template (i.e. linked reaction), it isfirst transcribed to mRNA. Alternatively mRNA could also be useddirectly for translation.

The template for cell-free protein synthesis can be either mRNA or DNA.Translation of stabilized mRNA or combined transcription and translationconverts stored information into a desired protein. The combined system,generally utilized in E. coli systems, continuously generates mRNA froma DNA template with a recognizable promoter. Either endogenous RNApolymerase is used, or an exogenous phage RNA polymerase, typically T7or SP6, is added directly to the reaction mixture. Alternatively, mRNAcan be continually amplified by inserting the message into a templatefor QB replicase, an RNA dependent RNA polymerase. Purified mRNA isgenerally stabilized by chemical modification before it is added to thereaction mixture. Nucleases can be removed from extracts to helpstabilize mRNA levels. The template can encode for any particular geneof interest.

Salts, particularly those that are biologically relevant, such asmanganese, potassium or ammonium, may also be added. The pH of thereaction is generally run between pH 6-9. The temperature of thereaction is generally between 20° C. and 40° C. These ranges may beextended.

In addition to the above components such as cell-free extract, genetictemplate, and amino acids, other materials specifically required forprotein synthesis may be added to the reaction. These materials mayinclude salts, polymeric compounds, cyclic AMP, inhibitors for proteinor nucleic acid degrading enzymes, inhibitors or regulators of proteinsynthesis, oxidation/reduction adjusters, non-denaturing surfactants,buffer components, spermine, spermidine, etc.

The salts preferably include potassium, magnesium, ammonium andmanganese salts of acetic acid or sulfuric acid, and some of these mayhave amino acids as a counter anion. The polymeric compounds may bepolyethylene glycol, dextran, diethyl aminoethyl dextran, quaternaryaminoethyl and aminoethyl dextran, etc. The oxidation/reduction adjustermay be dithiothreitol (DTT), ascorbic acid, glutathione and/or theiroxides. Further DTT may be used as a stabilizer to stabilize enzymes andother proteins, especially if some enzymes and proteins possess freesulfhydryl groups. Also, a non-denaturing surfactant such as TritonX-100 may be used at a concentration of 0-0.5 M. Spermine and spermidinemay be used for improving protein synthetic ability, and cAMP may beused as a gene expression regulator.

Synthesized product is usually accumulated in the bioreactor unit wandthen is isolated and purified according to the methods of the presentinvention for protein purification. The amount of protein produced in atranslation reaction can be measured in various fashions. One methodrelies on the availability of an assay that measures the activity of theparticular protein being translated. Examples of assays for measuringprotein activity are a luciferase assay system and a chloramphenicolacetyl transferase assay system. These assays measure the amount offunctionally active protein produced from the translation reaction.Importantly, activity assays will not measure full length protein thatis inactive due to improper protein folding or lack of other posttranslational modifications necessary for protein activity. As usedherein, the term “activity” refers to a functional activity oractivities of a peptide or portion thereof associated with a full-length(complete) protein. Functional activities include, but are not limitedto, catalytic or enzymatic activity, antigenicity (ability to bind orcompete with a polypeptide for binding to an anti-polypeptide antibody),immunogenicity, ability to form multimers, and the ability tospecifically bind to a receptor or ligand for the polypeptide.Preferably, the activity of produced proteins retain at least 55%, 60%,65%, 70%, 80%, 85%, 90%, 95% or more of the initial activity for atleast 3 days at a temperature from about 0° C. to 30° C.

Another method of measuring the amount of protein produced in a combinedin vitro transcription and translation reactions is to perform thereactions using a known quantity of radiolabeled amino acid such as³⁵S-methionine or ¹⁴C-leucine and subsequently measuring the amount ofradiolabeled amino acid incorporated into the newly translated protein.Incorporation assays will measure the amount of radiolabeled amino acidsin all proteins produced in an in vitro translation reaction includingtruncated protein products.

Biomolecules for Protein Expression

The following biomolecules are preferably used for protein expression.To carry out a protein expression reaction, energy components and aminoacids are supplied externally and may include, but not limited to thefollowing components:

-   -   A genetic template for the target protein (mRNA or DNA)        expression;    -   T7 RNA polymerases for mRNA transcription;    -   9 Translation factors (initiation, elongation and termination);    -   20 aminoacyl-tRNA synthetases (ARSes) for esterification of a        specific amino acid to form an aminoacyl-tRNA;    -   Methionyl-tRNA transformylase transfers hydroxymethyl-,        formyl-groups;    -   Creatine kinase converts ATP to ADP;    -   Myokinase catalyzes the inter conversion of adenine nucleotides;    -   Pyrophosphatase are acid anhydride hydrolases that act upon        diphosphate bonds;    -   4 nucleoside triphosphates (ATP, GTP, CTP, TTP) for DNA        formation;    -   Creatine phosphate which serves as a reserve of high-energy        phosphates for rapid mobilization;    -   10-formyl-5,6,7,8-tetrahydrofolate for the formylation of the        methionyl initiator tRNA (fMet-tRNA);    -   20 amino acids for protein synthesis;    -   Ribosomes for polypeptide translation;    -   46 tRNAs in protein synthesis; and    -   Cellular components which assist in proper protein folding.

Some of the proteins that may be expressed by the present invention foron-demand production may include, but not limited to,adrenocorticotropic hormone peptides, adrenomedullin peptides,allatostatin peptides, amylin peptides, amyloid beta-protein fragmentpeptides, angiotensin peptides, antibiotic peptides, antigenicpolypeptides, anti-microbial peptides, apoptosis related peptides,atrial natriuretic peptides, bag cell peptides, bombesin peptides, boneGLA peptides, bradykinin peptides, brain natriuretic peptides,C-peptides, C-type natriuretic peptides, calcitonin peptides, calcitoningene related peptides, CART peptides, casomorphin peptides, chemotacticpeptides, cholecystokinin peptides, colony-stimulating factor peptides,corticortropin releasing factor peptides, cortistatin peptides, cytokinepeptides, dermorphin peptides, dynorphin peptides, endorphin peptides,endothelin peptides, ETa receptor antagonist peptides, ETh receptorantagonist peptides, enkephalin peptides, fibronectin peptides, galaninpeptides, gastrin peptides, glucagon peptides, Gn-RH associatedpeptides, growth factor peptides, growth hormone peptides, GTP-bindingprotein fragment peptides, guanylin peptides, inhibin peptides, insulinpeptides, interleukin peptides, laminin peptides, leptin peptides,leucokinin peptides, luteinizing hormone-releasing hormone peptides,mastoparan peptides, mast cell degranulating peptides, melanocytestimulating hormone peptides, morphiceptin peptides, motilin peptides,neuro-peptides, neuropeptide Y peptides, neurotropic factor peptides,orexin peptides, opioid peptides, oxytocin peptides, PACAP peptides,pancreastatin peptides, pancreatic polypeptides, parathyroid hormonepeptides, parathyroid hormone-related peptides, peptide T peptides,prolactin-releasing peptides, peptide YY peptides, renin substratepeptides, secretin peptides, somatostatin peptides, substance Ppeptides, tachykinin peptides, thyrotropin-releasing hormone peptides,toxin peptides, vasoactive intestinal peptides, vasopressin peptides,and virus related peptides.

There is certainly a need for optimization and process developmentability at the microscale to help reduce cost of reagents and speed upbiotherapeutic manufacturing for translation into the clinic.⁹Microfluidic devices have offered a platform that could potentiallyserve this need, where less material is utilized to achieve similar endgoals and may allow for exploring novel approaches.^(10,11) The inherentscale enables the feasibility of developing portable, disposable andmodular chromatographic systems, where various chromatographic processescan be integrated into a single device.¹² Such versatile and modulardevices could be plugged in-line with other scale compatible devices forcharacterization and screening of proteins.

The combination of chromatographic techniques and microfluidics has beenreported for different purposes, proteins-on-demand, proteomicinvestigations, biomarker detection, nucleic acid investigation, andrapid optimization of separation techniques.^(9,13-17) Millet et al¹³have shown the modular microfluidics platform for protein purificationdemonstrating the use of affinity beads and size exclusionchromatography. However, conventional microfluidic device manufacturingis expensive, laborious and impossible without proper access tomicrofabrication facilities or machines. Also, the inherent scale ofmicrofluidic devices currently used for chromatography may not currentlybe practical, but are potentially scalable.^(11,14,15,18) There is apossibility for multiplexing with the current microscale technologies,but this still requires much effort towards usability.¹¹ Most of all,microfluidic devices in most cases are focusing on integrating withcurrent HPLC machines or mass spectrometry machines.

The present invention provides for versatile, customizable, robust,low-cost, and easily manufacturable chromatography columns for rapidscreening of therapeutic quality protein purification. The reportedscale addresses a huge gap in the current market between large (1 mL-1L) columns and very small (0.1-10 μL) low to high pressure microfluidiccolumns. The microscale column (μCol ranging from 25-200 μL) devicedescribed here is equipped to accommodate any affinity-based resin andserves as a universally compatible microfluidic unit for any system.These devices offer the ability to reduce reagent use, comparableprotein purity, higher throughput, and low dead volumes, compared toconventional columns in the market.¹⁹⁻²² The technology described hereinprovides a solution for quick prototyping of microscale columns forquick process development and optimization for affinity-basedpurification. As an example application, affinity His-Pur cobalt-NTA(ThermoFisherScientific Inc.) resin and columns were utilized foron-chip characterization and purification of granulocyte colonystimulating factor (G-CSF) protein, expressed using the cell-freeCHO-IVT system.

Design Considerations.

Most chromatographic methods rely heavily on the device geometries,geometric phases, and high-pressure separations. However, the advent ofmicrochips for chromatographic separations entails potential benefitsand the planar geometry has not stopped the evolution in chromatographicscreening methods in such systems. The planar format is the dominatingformat in the microfluidic separation devices, due to the ease offabrication and design.^(10,11) The planar format is a result ofavailable machining tools used to fabricate micro-devices, even thoughthis may not be an ideal situation for high-pressure operations ofpressure driven separations. The chemical interactions between resin andprotein are dominant in this situation and hence may be less dependenton the geometric design, but is not completely independent of channelgeometry.²⁹ To determine the optimal design parameters, the presentinvention focused on column arrays consisting of varied channelthicknesses and volumes. Devices were fabricated in polymethylmethacrylate (PMMA) substrates, off the shelf fittings (i.e. Luer lockfittings and PEEK fittings), PTFE frits and metal affinitychromatography resin (FIG. 10).

PMMA is a sturdy thermoplastic that is often the plastic of choice formicrofluidic purposes due to its good acid/base/solvent resistance, andexcellent optical properties.³⁰ The bonding method described herein wasadapted from a previously described method²³, where the method ofbonding involves solvent (ethanol) bonding at temperatures of 80-85° C.When using such temperature and solvent conditions, the bonding isirreversible and has shown to be mechanically sturdy at high operatingpressures.^(23,31,32) Techniques using PMMA are relatively simple toimplement in any laboratory setting and hence devices can be quicklyprototyped. Another major consideration when designing chromatographycolumns is the retention of chromatography resin within the separationchannel. To ensure proper retention of affinity beads inside the column,off-the shelf PTFE frits were bonded towards the outlet end of thecolumns. Such frits are commonly used in chromatography during thepacking protocols. There are two main iterations of μCol discussedherein, one chip was designed to bear varied volumes of resin (from25-200 μL) and the other chip bore 5 channels of 100 μL volume. Thesetwo iterations of chips demonstrate the versatility and customizabilityof this system, thus providing quick solutions for process optimization.μCols were packed using the LabSmith Inc. setup, where the pressure andflow rate was monitored in real-time. Labsmith Inc. system provides aneasily customizable platform and an easy interface for resin packingalong with pressure and flow rate measurements. This is the advantagewith the device presented herein, as well as its adaptability. Packingpressures were recorded to be between 20-40 kPa (˜3-6 psi) withoperation pressures reaching a maximum of 50 kPas (˜7.2 psi).

Column Performance and Computational Modeling.

Column validations included testing the packing efficiency, theoreticalplates, and protein purification profiles on a conventional HPLC. Postpacking, it is often necessary to test the integrity of the resin bed toconfirm the quality and consistency of the chromatographic operations.³³Several measurements are used to qualify a column; these parameters arenumber of theoretical plates for a column and asymmetrical ratio betweenthe two sections of a chromatographic peak. The most common type of testsignal applied is a pulse test function, where a small volume of atracer molecule is added to the buffer flowing through thecolumn^(33,34). The peak broadening over the column is measured usingheight equivalent to a theoretical plate (HETP) and peak symmetry alsodescribed by an asymmetric ratio (A). These parameters were tested using1% acetone injections where the peak shape and theoretical plates werecalculated from UV profiles from pulse tests (FIG. 11). These measuredprofiles were compared to conventional off the shelf 1 mL columns.Acetone injection tests revealed a trend where an increase in flow ratedecreased the theoretical plates for all tested column volumes. However,an increase in column volume did not result in a significant change.Although the theoretical plate numbers in μCols (31.5±12.6 platesmeasured through the HPLC software) seemed close to the range ofconventional columns (˜50 plates), the μCol peak shapes seemed muchsharper. The measurement of the asymmetric ratio (As), between theascending and descending portions of the acetone peaks at 10% of itspeak height is another standard method used to determine columnperformance and packing efficiency. μCol peak asymmetrical ratios weremeasured to be 1.5±0.1, compared to the conventional 1 mL column peakratios to be around 0.88. The ideal asymmetry peak ratio is 1, however,a typical acceptable range is between 0.8<A_(s)<1.8.^(33,35) Notably theCols found here in fall within this range, which suggests a positiverelationship to conventional column performance. In addition, COMSOL®multiphysics modeling and fluidic simulations successfully substantiatethe experimental μCols parameters using equation 1-9, explained before.FIG. 12 A illustrates the designed geometry and finite element mesh fora μCols with a single frit located at the outlet of the column. FIG. 12Bis a similar illustration of the same column but with frits located atthe inlet and outlet of the column. In FIG. 12 C, the COMSOL modelingresults for three various sizes of the column with a single frit at theoutlet were plotted. FIG. 12D, represents the comparison between thesingle frit versus the two frits micro-columns. By subtracting the peakvariance from extra-column sources and the feed variance contribution,the modeling results are seen to be in good agreement with theexperimental tests using 1% acetone. The calculated variance ofexperimental results was 0.00587 min² compared to the theoreticallymodelled variance of 0.00371 min² (Calculated through theoreticalmodeling, using Eq. 8 and 9, shown below). Computational modeling alsoproved useful in understanding how to improve the column performance bychanging the frit thickness parameters. Modeled data (FIG. 12E) revealedthat a smaller frit thickness of 0.5 mm might further improve theperformance compared to the 1.5 mm which is currently being used.However, a larger 2 mm frit thickness leads to further tailing of thecolumn peaks.

This indicates that the assumption used in the modeling that the columnpermeability and porosity were uniform inside column is valid. However,the lower end of the peak width generally provides a more symmetricalappearance of the peak and efforts are currently underway to improve thepacking efficiency to reduce plate heights. In addition to the peakperformance, protein purification efficiency was tested for Granulocytecolony stimulating factor (G-CSF) (FIG. 13 and FIG. 14). G-CSF usingμCols, resulted in similar or slightly better protein purity (93%)observed compared with conventional 1 mL column (>90%) (FIG. 13). μColsprovide an additional advantage due to their customizable size byconsiderably reducing impurities. Since affinity resin binding sitesmight be overwhelmed with protein of interest, the suggestion would beto fine tune the column capacity based on the known proteinconcentration and attain improved purity. Through literature, mostchromatography columns are range from less than 10 μL resin volume(microfluidic^(11-13,36)) most of which are not very compatible with aregular HPLC machine or above 1 mL resin volume at the other end of thespectrum.²⁰⁻²² The fabrication and manufacturing is often expensive andfabrication methods are not easily accessible to most research labs.This presents a huge gap in this area of research for a low-cost,customizable and versatile screening toolkit for protein purification ina workable range that is compatible with conventional HPLCs. To addressthis gap, μCol arrays were designed herein that are capable of holding avolume of affinity resin between 25-200 μL which can easily becustomized for a set amount of protein. Table 1, highlight theperformance of μCols compared with conventional 1 mL columns. Using theμCol array, the user is provided with customizable resin capacities thatcould match the protein concentration (Table 1). Customization can alsosave on considerably large amounts of buffer and run time foroptimization experiments. The amount of buffer used in this study forμCols was 10-fold less compared to conventional methods (e.g. 10 mL ofwash and elution buffer is needed for the conventional IMAC columns,whereas for the μCol, only needed 1 mL of each buffer was necessary)(Table 1). Purification times were reduced to 10-20 min (totalpurification run-time) from a typical run-time of 1-2 h. Potentially,such devices could be incorporated into a research or industry setting,where a newly discovered therapeutic or research grade protein israpidly optimized at low-cost. An added advantage over current methodsis that μCol devices contain HPLC compatible fittings and potentiallycan be used in tandem with all HPLC systems that use PEEK fittings (with10-32 UNF taps or Luer locks).

The present invention provides for the development of versatilemicrofluidic platforms for early-stage optimization of therapeuticprotein purification. Devices are compatible with most HPLC fittingsmaking them possible to use with any generic chromatography instruments.In addition, it is important to highlight that the manufacturing processis less expensive than conventional methods but with a resulting productof comparable performance. The sample purity and column efficiency ofthe μCols is comparable to conventional columns. These customizabledevices address a niche area for protein purification and processautomation. Besides protein capture with affinity resins, thismicroscale device can also be adapted for various other biomolecularseparation systems, such as ion exchange, size exclusion and bufferexchange chromatography by choosing the appropriate resin, columndesign, and volume necessary for optimal conditions. These columns canfind use in applications in various use cases such as biopharmaceuticaldrug development and point-of-care device.

Experimental Section

Materials.

PTFE frit (20 μm PTFE frits, Omnifit® Catalogue #OMNI006FR-06-20); HPLCto luer fittings (10-32 female to male luer fitting, IDEX, Catalogue#P-656), His-Pur IMAC resin (HisPur cobalt resin, Catalogue #89966,ThermoFisher Scientific), PMMA (Astra Product, Clarex©, PMMA sheets, 1mm and 1.5 mm); CHO cell-free IVT system (Thermo Scientific, MD, Catalog#CCS1031), 10 kDa MWCO Slide-A-Lyzer, 0.5 mL-3 mL capacity cassette(Thermo cassette, Thermo Scientific, Catalogue #66380); Luer lock caps(Female luer cap, polycarbonate, Cole parmer, #SC-45501-28), luer lockplug (Male luer lock plug, polycarbonate, #EW-45504-56), PTFE tubing(Cole Parmer 1/32″ ID× 1/16″OD, 25 ft/pk, #EW-06407-41), Ethanol,(Fisher Scientific, #04-355-451, 1 gal. 200 proof); Labsmith componentsfor 1/16″ ID, pressure sensor starter package for uPS Pressure sensor:uPS0800-800 kPa abs. range.

Device Design.

2D designs sketched in Corel draw were printed on PMMA sheets using aCO₂ laser printer CO₂ laser (Laser diode wavelength 630-680 nm, maxoutput is 5 mW, class laser 3R laser product, 2.0 lens module). Prior tobonding, each printed PMMA layer was rinsed with DI water and dried withkim-wipes, then cleaned using isopropanol wipes. The mico-Columns (μCol)were made up of three PMMA layers, top inlet outlet layer (1.5 mmthick), middle channel and a base plate (each 1 mm thick). The designconsists of the top 1.5 mm thick PMMA layer that has a large circularslot (6 mm diameter) towards the outlet end (meant for PTFE frits),middle 1 mm thick PMMA layer bearing the micro-channel to accommodatechromatography resin and bottom 1.5 mm PMMA base plate. Two devicedesigns were tested here, one had an array of microscale channelsconsisting of different volumes (25-200 μL) and the other had 5microscale channels consisting of one volume (100 μL), as shown in FIG.10.

Thermal Solvent Bonding Method.

Temperature regulated metal plates were custom fit to the top and bottomsurfaces of a Carver® press (Carver Hydraulic Press Model M). Prior todevice bonding these were pre-heated to 80° C. Each plate had atemperature controller managed by an external relay unit responsible formaintaining the temperature. Aluminum plates and silicon sheets werepre-heated to 80° C. Devices were sandwiched between aluminum plates,heated to 80° C. for 10 min. The process and apparatus used is shown anddescribed in FIG. 15. The solvent bonding using ethanol was adopted andmodified from a previously published articles by Al-Adhami etal.^(23,24) The device apparatus was then removed and allowed to cool atroom temperature. Each PTFE frit is 6 mm in diameter and 1.5 mm thickand fits perfectly into the designated slot. PTFE frits were simplyplaced inside each of its reserved slots. Luer lock cap fittings wereglued in place to hold the frits within each slot. Prior to attachingluer caps to the device, a hole was drilled through each of thesefittings using a 2.5 mm titanium drill bit (drill bit McMaster #39,titanium nitride kit) fixed to a Dayton™ 16″ drill press. The drilledluer lock fittings were cleaned with DI water and ethanol, air dried,and then glued to the inlet/outlets of each device. The luer fittingsenabled the connection of the μCol to the HPLC fittings, via the PEEK(luer to 10/32) fittings as shown and discussed in FIGS. 16 and 17.Devices were stored in a clean and sterile environment until used.

IMAC Resin Packing.

Resin packing protocol was specially developed to accommodate μColdevices. For this setup, two 10 mL BD syringes were required (fixed ontoa BASi syringe holder, BAS), 1/16″ inner diameter PTFE tubing, Omnifit3-way valve (Omnifit, Sigma Aldrich, Supelco, 56140-U), Labsmith®pressure sensors, Sensirion® flow sensor and a 4.0 psi check valve atthe outlet. Procedure was as follows: 1 mL of His-Pur cobalt beads wereresuspended into 40 mL of DI water in a conical (50 mL) tube. Themixture was gently shaken before being filled into a 10 mL loadingsyringe. 1-2 mL ethanol (10 mL syringe) was pushed through the device(0.5 mL/min flow rate) to wet the surface and remove any air-bubblesprior to adding the beads. (Apparatus and setup explained in FIG. 11 Band FIG. 12 A). The pressures and fluidic flow are monitored in realtime while His-beads accumulate inside the column as shown in FIG. 18.10-15 column volumes of 20% ethanol were pushed through the packeddevice at 0.5 mL/min, this ensured the tight packing of beads. Postpacking, devices were stored at 4° C. until used for validation andpurification experiments.

Column Validations on HPLC.

Column validation (packing efficiency, theoretical plates, pressure andflow rate profiles) were performed on an UltiMate 3000 HPLC system(ThermoFisher Scientific). The μCol performance was compared with theconventional 1 mL columns (Thermo Scientific His-Pur). 1% solution ofacetone in 20% ethanol (v/v) injections was used to validate the packingefficiency on the HPLC (See FIG. 14 and data presented in Table 1) Astandard solutions from 50 ug-400 ug was the range used to determine alinear range. All columns were validated, tested, and cleared for useprior to protein purifications. Graphical analysis and plots wereprepared using GraphPad Prism 7.

Computational Modeling and Simulations.

Computational modeling and fluidic flow simulations were conducted usingCOMSOL Multiphysics. Simulations were conducted for the μCols (length 27mm and the width of 0.98 mm), where the model consisted of six connectedcylinders, one of which represented the PTFE frit at the outlet (for theone-frit design) and two of which represented the frits at the inlet andoutlet (for the two-frit design) of the column. The fluid flow profileswithin the liquid-filled domains of the micro-column were determined bysolving the Navier-Stokes equation for incompressible flow given asfollows:

ρ({right arrow over (u)}.{right arrow over (∇)}){right arrow over(u)}=−{right arrow over (∇)}.[−pI +μ({right arrow over (∇)}{right arrowover (u)}+({right arrow over (∇)}{right arrow over (u)})^(T)]  (1)

In Eq. 1 μdenotes the dynamic viscosity, {right arrow over (u)} is thefluid velocity in the liquid-filled domain, ρ is the fluid density, andp is the pressure. Alternatively, the Brinkman equation shown by Eq. 2was used to determine the flow profiles in the particulate bed:

$\begin{matrix}{{\frac{\mu}{k}\overset{\rightharpoonup}{u}} = {\overset{\rightharpoonup}{\nabla}{.\left\lbrack {{{- p}\overset{=}{I}} + {\frac{\mu}{\alpha}\left( {{\overset{\rightharpoonup}{\nabla}\overset{\rightharpoonup}{u}} + \left( {\overset{\rightharpoonup}{\nabla}\overset{\rightharpoonup}{u}} \right)^{T}} \right)}} \right\rbrack}}} & (1)\end{matrix}$

In Eq. 2, k denotes the permeability of the column and a is itsporosity.The boundary conditions for Eqs. 1 and 2 are as follows:(i) Inlet velocity: {right arrow over (u)}={right arrow over (u)}₀(ii) No slip condition at the column wall: {right arrow over (u)}=0(iii) Outlet gauge pressure: p=0The mass transport of solute species i in the non-porous domains wasdetermined by solving the following two equations:

$\begin{matrix}{{\frac{\partial C_{i}}{\partial t} + {\overset{\rightharpoonup}{\nabla}{\cdot {\overset{\rightharpoonup}{N}}_{i}}}} = 0} & (3) \\{{\overset{\rightharpoonup}{N}}_{i} = {{{- \left( D_{e} \right)}{\overset{\rightharpoonup}{\nabla}C_{i}}} + {\overset{\rightharpoonup}{u}C_{i}}}} & (4)\end{matrix}$

In Eqs. 3 and 4, C_(i) is the concentration of species i in the fluid,{right arrow over (N)}_(i) is the molar flux of species i, and D_(e) isthe diffusion coefficient.

To account for the mass transport of solute species i in the particulatebed, the combined effect of convective diffusion and dispersion in theinterparticle fluid and diffusion in the particles was determined bysolving Eqs. 5 and 6:

$\begin{matrix}{{{\alpha\frac{\partial C_{i}^{i}}{\partial t}} + {\overset{\rightharpoonup}{\nabla}{\cdot {\overset{\rightharpoonup}{N}}_{i}^{s}}}} = R_{i}^{s}} & (5) \\{{\overset{\rightharpoonup}{N}}_{i}^{s} = {{{- \left( {{\overset{=}{D}}_{D}^{S} + {\overset{=}{D}}_{e}^{S}} \right)}{\overset{\rightharpoonup}{\nabla}C_{i}^{i}}} + {{\overset{\rightharpoonup}{u}}_{i}^{s}C_{i}^{i}}}} & (6)\end{matrix}$

In Eqs. 5 and 6, C_(i) ^(i) indicates the interstitial concentration ofspecies i (i.e. the concentration of species i in the interparticlefluid), {right arrow over (N)}_(i) ^(s) is the superficial molar flux ofspecies i, {right arrow over (u)}_(i) ^(s) is the superficial fluidvelocity and D _(D) is the superficial dispersion coefficient diagonaltensor. Note that the term “superficial” denotes a quantity evaluatedper unit volume of particulate bed or per unit cross-sectional area ofparticulate bed. The Peclet numbers of 20 and 0.5 were used to determinethe axial and radial components of the dispersion coefficient tensor,respectively.^(25,26)

In Eq. 5, R_(i) ^(s) is the superficial adsorption rate that isdetermined by assuming a parabolic concentration profile inside theparticle. This assumption results in a Linear Driving Force (LDF)approximation described as follows:

$\begin{matrix}{R_{i}^{s} = {\left( {1 - \alpha} \right)\frac{60*D_{i,{particle}}}{d_{p}}\left( {q_{i} - {f\left( C_{i}^{i} \right)}} \right)}} & (7)\end{matrix}$

where D_(i, particle) is the diffusion coefficient of species i in theparticle, d_(p) is the particle diameter, q, is the averageconcentration in the particle, and f(C_(i) ^(i)) is the equilibriumvalue of q_(i) for a given value of C_(i) ^(i). The initialconcentration of zero for C_(i) ^(i) was assumed and Eq. 1-7 were solvedsimultaneously together with the boundary conditions mentioned above forthe case of a rectangular solute injection volume.

To compare the performance of the μCols, the number of theoreticalplates (N) was calculated based on the Foley-Dorsey equation as follows:

$\begin{matrix}{N = \frac{{1.8}3\left( {t_{R}/w_{0.5}} \right)^{2}}{\left( \frac{B}{A} \right)_{0.5} - {0.7}}} & (8)\end{matrix}$

where t_(R) is the retention time at the peak maximum, w_(0.5) is thepeak width at the 50% peak height and (B/A)_(0.5) is the asymmetryfactor at the 50% peak height.

The variance (σ²) was then calculated according to the Eq. 9:

$\begin{matrix}{\sigma^{2} = \frac{t_{R}^{2}}{N}} & (9)\end{matrix}$

The approach used in this study for modeling the mass transport withinthe micro-column has two advantages compared with previous similarstudies.²⁵⁻²⁶ First, non-linear adsorption equilibrium can be includedin the modeling using the LDF approximation for species transport, asopposed to the use solely of linear equilibrium as considered inprevious models, and second the dispersion coefficient has been definedseparately for the axial and radial directions inside the column, whichmakes the modeling results more realistic since these dispersioncoefficients typically vary by an order of magnitude or more.

In Vitro Protein Expression (IVT) System.

The IVT system has three components: (a) the commercially available CHOcell-free lysate; (b) the reaction mixture consisting of ingredientsneeded for the transcription and translation of the target gene and (c)the dialysis buffer, which contains reaction supplements and energyregenerating material required to support protein expression in acontinuous exchange system. The IVT system uses a 10 kDa MWCOSlide-A-Lyzer, 0.5 mL-3 mL capacity cassette as a modified bioreactordevice. It provides a constant supply of energy-regenerating substratesto maintain the reaction while removing toxic byproducts. Procedure ofpreparing the reaction mix was adopted from previously publisheddata^(27,28) and slightly modified as follows: 1 mL vial of IVT CHOlysate is thawed and reconstituted with 435 μL nuclease free water, 5 μLof GADD34myc, 400 μL of reaction mix (with DTT) and finally 160 μL(containing 80 μg) solution of protein (GFP) DNA, sequentially). Thetotal reaction mix of 2 mL is split evenly between two 3.0 mL capacitydialysis cassettes. This provides an increased surface to volume ratiobetween the reaction mix and dialysis buffer. Cassettes are sealedinside the dialysis bag and placed inside an orbital shaker incubatorfor 6 h at 30° C. and 150 rpm (Sartorius shaker incubator, Certomat®BS-1, Sartorius).

Protein Purification.

Purification of G-CSF were performed on the HPLC (UltiMate 3000 HPLCsystem, ThermoFisher Scientific). Prior to loading protein, columns weresaturated with wash buffer 1 (prepared in 1× Phosphate buffered saline(PBS) contains 10 mM of Imidazole (pH adjusted to 7.4)) for 15 columnvolumes (CVs) at 0.5 μL/min flow rate. After which, GCSF was loaded onthe column using a syringe pump, at a flow rate of 0.2 mL/min. Postloading, the impurities were washed of the columns using wash buffer 2(prepared in 1×PBS contains 40 mM of Imidazole and 300 mM Sodiumchloride (NaCl) (pH adjusted to 7.4) for 10 CVs at 0.5 mL/min. Finally,the protein was eluted out (elution buffer was prepared in 1×PBScontains 200 mM of Imidazole (pH adjusted to 7.4) at 0.5 mL/min. Thetotal eluted volume collected from the μCol was 0.5 mL compared to2.3-2.5 mL of sample collected from the 1 mL Thermo columns. The elutedsamples were analyzed by silver stained SDS-PAGE gels to verify theextent of impurities within each of the repeats. From the silver stains,there is evidence of purity and consistency between repeats for the 0.3and 0.5 mL G-CSF harvest samples (Table 2). In addition, the westernblots indicate the presence of protein of interest G-CSF and show theconsistency in the band intensity between samples. The 660 assaysprovided an idea about the consistent amounts collected from each μCol.

Protein Analysis.

Western Blot:

Samples were diluted in phosphate buffered saline and glycerol (PBS, pH7.4). In a fresh 1.5 mL Eppendorf tube, 15-18 μL of PBS+glycerolsolution was aliquoted and to this a 2-5 μL of sample was mixedtogether. This was then treated with 6 μL of 5× diluted Laemmli bufferdye, then boiled at 100° C. for 5 minutes, then loaded to a pre-cast4-20% Criterion XGT gel and run at 250V for 30 min, with a pre-run of 10min. After gel has been run, the cassette is cracked, and the gel istransferred into the blotting apparatus immersed in 1× Tris-Glycinetransfer buffer). This helps transfer the proteins onto a nitrocellulosemembrane (Bio-rad, Cat. #1620233). Once removed from the apparatusproteins are left in 20 mL blocking buffer overnight with an anti-G-CSFprimary antibody.

Primary antibody (Rabbit anti-G-CSF, Abcam, Cat. #9691) at aconcentration of 1:3000 to 20 mL blocking buffer was added to theblocking buffer and left overnight. The following day this was removed,and the blot was washed with a solution of PBS containing 0.1% Tween(PBST). Fresh blocking buffer (20 mL) was then added with acomplementary HRP-conjugated secondary antibody (Goat Anti-Rabbit HRP,Abcam, Cat. #ab6721) at a concentration of 1:3000 and left mixing for 1h. The blot was subsequently washed with PBST a couple of times.Finally, a chemiluminescent substrate (Thermo Scientific, Cat. #34075)was added to the blot and imaged using a ThermoScientific myECL™ Imager.

Silver Stains.

Protein gels were prepared similar the western blot protocol. The Silverstaining was performed on purified G-CSF samples using a ProteoSilver™plus silver stain kit (Sigma-Aldrich, cat. #PROTSIL2). Criterion TGX™precast midi protein gel (4-20%) (Bio-Rad, cat. #1656001) was used forthese silver staining experiments following standard protocol with aCriterion™ electrophoresis cell (Bio-Rad, cat. no. #5671093). was used.Known concentrations of G-CSF (Life Technologies,) were loaded as astandard reference for determining the presence of purified protein ofinterest. Percent purity was determined using image analysis software bytaking the ratio of the area of the known, lowest detectable G-CSF-Hisband vs. the total area, where the total area is equal to the area ofthe lowest detectable G-CSF-His band+area of impurities in an overloadedgel.

660 nm assay. Analysis was done using Pierce 660 nm protein assay kit(Thermo Scientific, Cat. #22660) following standard protocol. BSAstandard solutions 50-1000 μg/mL were used for determining theconcentrations of sample protein.

REFERENCES

The references cited herein are incorporated by references herein forall purposes.

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TABLE 1 μCol (volume Column Conditions 25-200 μL) Thermo column BindingCapacity ~1 mg ~10 mg Volume 0.025-0.1 mL 1 mL Wash buffer 1 (15 CVwash) 0.38-1.5 mL 15 mL Wash buffer 2 (10 CV wash) 0.25-1 mL 10 mLEluted Volume 0.25-1 mL 2.5 mL Total Purification time 10-20 min 2 hPurity of eluted protein 93.4 ± 1.4  ≥90 Theoretical Plates(for flow31.5 ± 12.6 ~50 rates between 0.1-0.5 ml/min) Asymmetrical ration (forflow 1.5±     0.88 rates between 0.1-0.5 ml/min) Manufacturer CAST, UMBCPierce-ThermoFisher Scientific Cost of each device $5-15 $30-50

TABLE 2 Protein Concentration Expres- (μg/mL) Area under Column sionSilver Western 660 nm assay the curve Type (mL) n strains Blots Mean ±StDev μCol 0.3 4 + + 71.48 ± 7.07 40.95 ± 5.84 μCol 0.5 3 + + 65.66 ±2.8  47.62 ± 3.16 μCol 0.5 1 − − − 1.25 (blank)

That which is claimed is:
 1. A factory-on-a-chip microfluidic devicecomprising: (i) a microfluidic bioreactor unit equipped with acontinuous collection channel for a synthesizing a crude protein in areaction within the microfluidic bioreactor unit; (ii) a microfluidicmixer/de-bubbler unit communicatively connected to the microfluidicbioreactor unit to dilute the crude protein and remove any air bubblesduring mixing; and (iii) a microfluidic purification unitcommunicatively connected to the microfluidic mixer/de-bubbler unitcomprising at least one purification column capturing the crude proteinand providing a purified protein.
 2. The factory-on-a-chip microfluidicdevice according to claim 1, further comprising at least one processanalytical technology (PAT) sensor for monitoring pH, pressure,temperature, dissolved-oxygen, redox conditions, ionic strength, UV-Visabsorbance, fluorescence, light scatter, and/or circular dichroismconditions during the reaction, purification and/or analysis of thecrude and/or purified protein, wherein the at least one sensor iscommunicatively connected to the a microfluidic bioreactor unit and/ormicrofluidic purification unit.
 3. The factory-on-a-chip microfluidicdevice according to claim 1, wherein the mixer/de-bubbler comprises aporous membrane to eliminate bubbles.
 4. The factory-on-a-chipmicrofluidic device according to claim 1, wherein the units (i), (ii),and (iii) are stacked together to form a single unit.
 5. Thefactory-on-a-chip microfluidic device according to claim 4, wherein thesingle unit has a dimensional length of about 100 mm to 150 mm and awidth perpendicular to the length of about 40 mm to about 90 mm.
 6. Thefactory-on-a-chip microfluidic device according to claim 1, wherein themicrofluidic purification unit comprising 4 to 8 purification columns.7. The factory-on-a-chip microfluidic device according to claim 1,wherein the at least one purification column comprises chromatographyresin for capturing the crude protein.
 8. The factory-on-a-chipmicrofluidic device according to claim 7, wherein the chromatographyresin is an immobilized metal affinity resin and an ion exchange resin.9. The factory-on-a-chip microfluidic device according to claim 1,wherein the microfluidic bioreactor comprises lyophilized cell extractsand reagents for expression of the crude protein.
 10. Thefactory-on-a-chip microfluidic device according to claim 7, wherein theat least one purification column further comprises solutions for anelution buffer for harvesting the purified protein.
 11. Thefactory-on-a-chip microfluidic device according to claim 1, wherein theat least one purification column is a micro-column having microscalechannels for a volume ranging from about 25-200 μL.
 12. Thefactory-on-a-chip microfluidic device according to claim 11, wherein themicro-column is fabricated of three polymethyl methacrylate (PMMA)layers comprising a top layer, a middle layer comprising a channel and abase plate.
 13. The factory-on-a-chip microfluidic device according toclaim 12, wherein the top layer is about 1 to about 2 mm thick, themiddle layer about 0.75 to about 1.25 mm comprising the a micro-channelto accommodate chromatography resin and the base plate is about 1 toabout 2 mm.
 14. A method of preparing and administering a therapeuticprotein on demand to a subject, the method comprising: (a) synthesizingthe therapeutic protein with a microfluidic factory on a chipcomprising: (i) a microfluidic bioreactor unit equipped with acontinuous collection channel for a synthesizing a crude protein in areaction within the microfluidic bioreactor unit, wherein themicrofluidic bioreactor unit comprises cell extracts and reagents forexpression of the crude protein; (ii) a microfluidic mixer/de-bubblerunit communicatively connected to the microfluidic bioreactor unit todilute the crude protein and remove any air bubbles during mixing; and(iii) a microfluidic purification unit communicatively connected to themicrofluidic mixer/de-bubbler unit comprising at least one purificationcolumn comprising chromatography resin and for capturing the crudeprotein and providing the purified therapeutic protein; and (b)administering the purified therapeutic protein to the subject in asufficient amount of time to maintain the viability of the purifiedtherapeutic protein.
 15. The method according to claim 14, wherein thepurified therapeutic protein is delivered to the subject within onehour, one day or one week.
 16. The method according to claim 14, whereinthe cell extracts comprise a combination of cytoplasmic and/or nuclearcomponents from cells comprising reactants for protein synthesis,transcription, translation, DNA replication.
 17. The method according toclaim 14, wherein the factory-on-a-chip microfluidic device furthercomprising further comprising at least one process analytical technology(PAT) sensor for monitoring pH, pressure, temperature, dissolved-oxygen,redox conditions, ionic strength, UV-Vis absorbance, fluorescence, lightscatter, and/or circular dichroism conditions during the reaction,purification and/or analysis of the crude and/or purified protein,wherein the at least one sensor is communicatively connected to the amicrofluidic bioreactor unit and/or microfluidic purification unit. 18.The method according to claim 14, wherein the mixer/de-bubbler comprisesa porous membrane to eliminate bubbles.
 19. The method according toclaim 14, wherein the units (i), (ii), and (iii) are stacked together toform a single unit.
 20. The method according to claim 19, wherein thesingle unit has a dimensional length of about 100 mm to 150 mm and awidth perpendicular to the length of about 40 mm to about 90 mm.
 21. Themethod according to claim 14, wherein the microfluidic purification unitcomprising 4 to 8 purification columns.
 22. The method according toclaim 14, wherein the at least one purification column compriseschromatography resin for capturing the crude protein.
 23. The methodaccording to claim 22, wherein the chromatography resin is animmobilized metal affinity resin and an ion exchange resin.
 24. Themethod according to claim 22, wherein the at least one purificationcolumn further comprises solutions for an elution buffer for harvestingthe purified protein.
 25. The method according to claim 14, wherein theat least one purification column is a micro-column having microscalechannels for a volume ranging from about 25-200 μL.
 26. The methodaccording to claim 25, wherein the micro-column is fabricated of threepolymethyl methacrylate (PMMA) layers comprising a top layer, a middlelayer comprising a channel and a base plate.
 27. The method according toclaim 26, wherein the top layer is about 1 to about 2 mm thick, themiddle layer about 0.75 to about 1.25 mm comprising the a micro-channelto accommodate chromatography resin and the base plate is about 1 toabout 2 mm.